Energy-delivery devices with flexible fluid-cooled shaft, inflow / outflow junctions suitable for use with same, and systems including same

ABSTRACT

An energy-delivery device suitable for delivery of energy to tissue includes an antenna assembly, a chamber defined about the antenna assembly, and a cable having a proximal end suitable for connection to an electrosurgical energy source. The energy-delivery device also includes a flexible, fluid-cooled shaft coupled in fluid communication with the chamber. The flexible, fluid-cooled shaft is configured to contain a length of the cable therein and adapted to remove heat along the length of the cable during delivery of energy to the antenna assembly.

CROSS-REFERENCE TO RELATED APPLICATIONS

The present application is a continuation application of U.S. patent application Ser. No. 14/688,086 filed on Apr. 16, 2015, which is a continuation application of U.S. patent application Ser. No. 12/985,124 filed on Jan. 5, 2011, now U.S. Pat. No. 9,011,421, the entire contents of each of which are incorporated herein by reference.

BACKGROUND 1. Technical Field

The present disclosure relates to electrosurgical devices suitable for use in tissue ablation applications and, more particularly, to energy-delivery devices with a flexible, fluid-cooled shaft, inflow/outflow junctions suitable for use with the same, and systems including the same.

2. Discussion of Related Art

Treatment of certain diseases requires the destruction of malignant tissue growths, e.g., tumors. Electromagnetic radiation can be used to heat and destroy tumor cells. Treatment may involve inserting ablation probes into tissues where cancerous tumors have been identified. Once the probes are positioned, electromagnetic energy is passed through the probes into surrounding tissue.

In the treatment of diseases such as cancer, certain types of tumor cells have been found to denature at elevated temperatures that are slightly lower than temperatures normally injurious to healthy cells. Known treatment methods, such as hyperthermia therapy, heat diseased cells to temperatures above 41° C. while maintaining adjacent healthy cells below the temperature at which irreversible cell destruction occurs. These methods involve applying electromagnetic radiation to heat, ablate and/or coagulate tissue. Microwave energy is sometimes utilized to perform these methods. Other procedures utilizing electromagnetic radiation to heat tissue also include coagulation, cutting and/or ablation of tissue.

Electrosurgical devices utilizing electromagnetic radiation have been developed for a variety of uses and applications. A number of devices are available that can be used to provide high bursts of energy for short periods of time to achieve cutting and coagulative effects on various tissues. There are a number of different types of apparatus that can be used to perform ablation procedures. Typically, microwave apparatus for use in ablation procedures include a microwave generator that functions as an energy source, and a microwave surgical instrument (e.g., microwave ablation probe) having an antenna assembly for directing energy to the target tissue. The microwave generator and surgical instrument are typically operatively coupled by a cable assembly having a plurality of conductors for transmitting microwave energy from the generator to the instrument, and for communicating control, feedback and identification signals between the instrument and the generator.

There are several types of microwave probes in use, e.g., monopole, dipole and helical, which may be used in tissue ablation applications. In monopole and dipole antenna assemblies, microwave energy generally radiates perpendicularly away from the axis of the conductor. Monopole antenna assemblies typically include a single, elongated conductor. A typical dipole antenna assembly includes two elongated conductors that are linearly-aligned and positioned end-to-end relative to one another with an electrical insulator placed therebetween. Helical antenna assemblies include helically-shaped conductor configurations of various dimensions, e.g., diameter and length. The main modes of operation of a helical antenna assembly are normal mode (broadside), in which the field radiated by the helix is maximum in a perpendicular plane to the helix axis, and axial mode (end fire), in which maximum radiation is along the helix axis.

The particular type of tissue ablation procedure may dictate a particular ablation volume in order to achieve a desired surgical outcome. Ablation volume is correlated with antenna design, antenna performance, antenna impedance, ablation time and wattage, and tissue characteristics, e.g., tissue impedance.

Fluid-cooled or dielectrically-buffered microwave devices may be used in ablation procedures. Cooling the ablation probe may enhance the overall heating pattern of the antenna, prevent damage to the antenna and prevent harm to the clinician or patient. Because of the small temperature difference between the temperature required for denaturing malignant cells and the temperature normally injurious to healthy cells, a known heating pattern and precise temperature control is needed to lead to more predictable temperature distribution to eradicate the tumor cells while minimizing the damage to surrounding normal tissue.

During certain procedures, it can be difficult for the surgeon to deploy an ablation probe, e.g., between closely spaced boundaries of tissue structures, to reach the location of the ablation site. Currently available microwave ablation devices may not be suitable for use during open surgical procedures when the surgeon is trying to ablate a lesion that is not easily accessed via a midline incision. A cable assembly connecting the ablation probe to a generator may come into contact with a patient and may facilitate potentially unwanted heat transfer.

SUMMARY

The present disclosure relates to an energy-delivery device suitable for delivery of energy to tissue including an antenna assembly, a chamber defined about the antenna assembly, and a cable assembly having a proximal end suitable for connection to an electrosurgical energy source. The energy-delivery device also includes a flexible, fluid-cooled shaft coupled in fluid communication with the chamber. The flexible, fluid-cooled shaft is configured to contain a length of the cable assembly therein and adapted to remove heat along the length of the cable assembly during delivery of energy to the antenna assembly.

The present disclosure also relates to an ablation device including a feedline and an antenna assembly. The feedline includes an inner conductor having a distal end, an outer conductor coaxially disposed around the inner conductor and having a distal end, and a dielectric material disposed therebetween. The antenna assembly includes an electrically-conductive proximal arm having a proximal end and a distal end, and an electrically-conductive distal arm including a proximal portion having an outer diameter and a distal portion having an outer diameter less than the outer diameter of the proximal portion. The proximal end of the proximal arm is electrically coupled to and coaxially disposed about the distal end of the outer conductor. The antenna assembly also includes a junction member. The proximal arm and the distal arm align at the junction member and are spaced apart a length by the junction member, thereby defining a feed gap therebetween.

The present disclosure also relates to a system including an electrosurgical energy source and an ablation device operably associated with the electrosurgical energy source. The ablation device includes a feedline and an antenna assembly operatively coupled to the feedline. The feedline includes an inner conductor having a distal end, an outer conductor coaxially disposed around the inner conductor and having a distal end, and a dielectric material disposed therebetween. The antenna assembly includes an electrically-conductive proximal arm having a proximal end and a distal end, and an electrically-conductive distal arm including a proximal portion having an outer diameter and a distal portion having an outer diameter less than the outer diameter of the proximal portion. The proximal end of the proximal arm is electrically coupled to and coaxially disposed about the distal end of the outer conductor. The proximal arm defines a first cavity therein extending from the distal end of the outer conductor to the distal end of the proximal arm. The proximal portion of the distal arm defines a second cavity therein. The antenna assembly also includes a junction member at least partially disposed in the first and second cavities. The proximal arm and the distal arm align at the junction member and are spaced apart a length by the junction member, thereby defining a feed gap therebetween.

The present disclosure also relates to an inflow/outflow junction suitable for connection to a first tubular member disposed around a transmission line and defining a fluid inflow conduit therebetween and a second tubular member disposed around the first tubular member and defining a fluid outflow conduit therebetween. The inflow/outflow junction includes a housing adapted to be coupled in fluid communication with a coolant supply system. The housing includes an outer wall and an inner wall cooperatively defining a fluid inlet chamber and a fluid outlet chamber. The inner wall is configured to define an opening in the fluid inlet chamber to allow the fluid inlet chamber to be connectable in fluid communication with the fluid inflow conduit. The outer wall is configured to define an opening in the fluid outlet chamber to allow the fluid outlet chamber to be connectable in fluid communication with the fluid outflow conduit.

The present disclosure also relates to a system including an electrosurgical energy source and an energy-delivery device operably associated with the electrosurgical energy source. The energy-delivery device includes an end-cap assembly defining a chamber therein, an antenna assembly disposed in the chamber; and a cable assembly configured to deliver energy from the electrosurgical energy source to the antenna assembly. The system also includes a flexible, extendable/retractable fluid-cooled shaft coupled in fluid communication with the chamber, wherein the flexible, extendable/retractable fluid-cooled shaft is configured to contain a length of the cable assembly therein and adapted to remove heat along the length of the cable assembly during delivery of energy to the antenna assembly.

BRIEF DESCRIPTION OF THE DRAWINGS

Objects and features of the presently disclosed energy-delivery devices with a flexible, fluid-cooled shaft and systems including the same will become apparent to those of ordinary skill in the art when descriptions of various embodiments thereof are read with reference to the accompanying drawings, of which:

FIG. 1 is a schematic diagram of an electrosurgical system including an energy-delivery device with a flexible, fluid-cooled shaft in accordance with an embodiment of the present disclosure;

FIG. 2A is an enlarged, cross-sectional view of the indicated area of detail of FIG. 1 showing a portion of a flexible, fluid-cooled shaft and an inflow/outflow junction adapted to be coupled in fluid communication therewith in accordance with an embodiment of the present disclosure;

FIG. 2B is an enlarged, cross-sectional view of another embodiment of an inflow/outflow junction adapted to be coupled in fluid communication the flexible, fluid-cooled shaft of FIG. 1 in accordance with the present disclosure;

FIG. 2C is an enlarged, cross-sectional view of yet another embodiment of an inflow/outflow junction adapted to be coupled in fluid communication the flexible, fluid-cooled shaft of FIG. 1 in accordance with the present disclosure;

FIG. 3 is an enlarged, cross-sectional view of the indicated area of detail of FIG. 1 showing a portion of a flexible, fluid-cooled shaft and an energy-delivery device adapted to be coupled in fluid communication therewith in accordance with an embodiment of the present disclosure;

FIG. 4 is a cross-sectional view of a portion of a flexible, extendable/retractable fluid-cooled shaft and an inflow/outflow junction adapted to be coupled in fluid communication therewith in accordance with an embodiment of the present disclosure;

FIG. 5 is a schematic diagram of the flexible, extendable/retractable fluid-cooled shaft and the inflow/outflow junction of FIG. 4 shown in a retracted configuration in accordance with an embodiment of the present disclosure; and

FIG. 6 is a schematic diagram of the flexible, extendable/retractable, fluid-cooled shaft and the inflow/outflow junction of FIG. 4 shown in an extended configuration in accordance with an embodiment of the present disclosure.

DETAILED DESCRIPTION

Hereinafter, embodiments of energy-delivery devices with a flexible, fluid-cooled shaft and systems including the same of the present disclosure are described with reference to the accompanying drawings. Like reference numerals may refer to similar or identical elements throughout the description of the figures. As shown in the drawings and as used in this description, and as is traditional when referring to relative positioning on an object, the term “proximal” refers to that portion of the apparatus, or component thereof, closer to the user and the term “distal” refers to that portion of the apparatus, or component thereof, farther from the user.

This description may use the phrases “in an embodiment,” “in embodiments,” “in some embodiments,” or “in other embodiments,” which may each refer to one or more of the same or different embodiments in accordance with the present disclosure. For the purposes of this description, a phrase in the form “A/B” means A or B. For the purposes of the description, a phrase in the form “A and/or B” means “(A), (B), or (A and B)”. For the purposes of this description, a phrase in the form “at least one of A, B, or C” means “(A), (B), (C), (A and B), (A and C), (B and C), or (A, B and C)”.

Electromagnetic energy is generally classified by increasing energy or decreasing wavelength into radio waves, microwaves, infrared, visible light, ultraviolet, X-rays and gamma-rays. As it is used in this description, “microwave” generally refers to electromagnetic waves in the frequency range of 300 megahertz (MHz) (3×10⁸ cycles/second) to 300 gigahertz (GHz) (3×10¹¹ cycles/second). As it is used in this description, “ablation procedure” generally refers to any ablation procedure, such as, for example, microwave ablation, radiofrequency (RF) ablation, or microwave or RF ablation-assisted resection.

As it is used in this description, “energy applicator” generally refers to any device that can be used to transfer energy from a power generating source, such as a microwave or RF electrosurgical generator, to tissue. For the purposes herein, the term “energy applicator” is interchangeable with the term “energy-delivery device”. As it is used in this description, “transmission line” generally refers to any transmission medium that can be used for the propagation of signals from one point to another. As it is used in this description, “fluid” generally refers to a liquid, a gas or both.

As it is used in this description, “length” may refer to electrical length or physical length. In general, electrical length is an expression of the length of a transmission medium in terms of the wavelength of a signal propagating within the medium. Electrical length is normally expressed in terms of wavelength, radians or degrees. For example, electrical length may be expressed as a multiple or sub-multiple of the wavelength of an electromagnetic wave or electrical signal propagating within a transmission medium. The wavelength may be expressed in radians or in artificial units of angular measure, such as degrees. The electric length of a transmission medium may be expressed as its physical length multiplied by the ratio of (a) the propagation time of an electrical or electromagnetic signal through the medium to (b) the propagation time of an electromagnetic wave in free space over a distance equal to the physical length of the medium. The electrical length is in general different from the physical length. By the addition of an appropriate reactive element (capacitive or inductive), the electrical length may be made significantly shorter or longer than the physical length.

Various embodiments of the present disclosure provide an energy-delivery device with a flexible, fluid-cooled shaft. Embodiments may be suitable for utilization in open surgical applications. Embodiments may be suitable for utilization with hand-assisted, endoscopic and laparoscopic surgical procedures. Embodiments may be implemented using electromagnetic radiation at microwave frequencies, RF frequencies or at other frequencies. An electrosurgical system including the presently disclosed energy-delivery device with a flexible, fluid-cooled shaft disposed in fluid communication with a coolant supply system via an inflow/outflow junction 51 according to various embodiments is designed and configured to operate at frequencies between about 300 MHz and about 10 GHz.

Various embodiments of the presently disclosed energy-delivery device with a flexible, fluid-cooled shaft are suitable for microwave or RF ablation and for use to pre-coagulate tissue for microwave or RF ablation-assisted surgical resection. Although various methods described hereinbelow are targeted toward microwave ablation and the complete destruction of target tissue, it is to be understood that methods for directing electromagnetic radiation may be used with other therapies in which the target tissue is partially destroyed or damaged, such as, for example, to prevent the conduction of electrical impulses within heart tissue. In addition, although the following description describes the use of a dipole microwave antenna, the teachings of the present disclosure may also apply to a monopole, helical, or other suitable type of microwave antenna or RF electrode.

FIG. 1 shows an electrosurgical system 10 according to an embodiment of the present disclosure that includes an energy applicator or probe 100 with a flexible, fluid-cooled shaft 110 coupled in fluid communication with a coolant supply system 150 via an inflow/outflow junction 51. An embodiment of an energy applicator, such as the probe 100 of FIG. 1, in accordance with the present disclosure, is shown in more detail in FIG. 3. It is to be understood, however, that other probe embodiments may also be used.

Probe 100, which is described in more detail later in this disclosure, generally includes an antenna assembly 12 having a distal radiating portion (e.g., “R” shown in FIG. 3). As shown in FIG. 1, the probe 100 is operably coupled by a flexible, transmission line 15 (also referred to herein as a cable assembly) to a connector 14, which further operably connects the probe 100 to an electrosurgical power generating source 28, e.g., a microwave or RF electrosurgical generator. Cable assembly 15 may include a proximal end suitable for connection to the electrosurgical power generating source 28. At least a portion of the cable assembly 15 (e.g., a length that may potentially transfer heat to a patient's body during a procedure) is disposed within the flexible, fluid-cooled shaft 110.

In some embodiments, the probe 100 includes a balun structure (e.g., “B” shown in FIG. 3). Balun structure “B”, which is described in more detail later in this disclosure, generally includes a balun insulator (e.g., 340 shown in FIG. 3) and a conductive balun sleeve (e.g., 350 shown in FIG. 3) disposed around the outer peripheral surface of the balun insulator, or portions thereof, and may include a balun short (e.g., 351 shown in FIG. 3).

According to various embodiments, the flexible, fluid-cooled shaft 110 is configured to circulate coolant fluid “F”, e.g., saline, water or other suitable coolant fluid, to remove heat that may generated along the length of the cable assembly 15, or portions thereof, during the delivery of energy, e.g., RF or microwave energy, to the probe 100. As cooperatively shown in FIGS. 1 and 2A, the shaft 110 includes a cable assembly 15, an inner tubular member 231 disposed around the cable assembly 15 and defining a lumen or fluid inflow conduit 331 therebetween, and an outer tubular member 235 disposed around the inner tubular member 231 and defining a lumen or fluid outflow conduit 335 therebetween. Outer tubular member 235 and the inner tubular member 231 are adapted to circulate coolant fluid “F” therethrough, and may include baffles, multiple lumens, flow restricting devices, or other structures that may redirect, concentrate, or disperse flow depending on their shape. In some embodiments, the inner tubular member 231 is coaxially disposed about the cable assembly 15, and the outer tubular member 235 is coaxially disposed about the inner tubular member 231. The size and shape of the inner tubular member 231, the outer tubular member 235, the fluid inflow conduit 331, and fluid outflow conduit 335 may be varied from the configuration depicted in FIG. 2A.

In some embodiments, at least a portion of the inner tubular member 231 and/or at least a portion of the outer tubular member 235 (e.g., a distal portion) may include an integrated, spiraling metallic wire to add shape-memory properties to the flexible, fluid-cooled shaft 110, e.g., to aid in placement of the probe 100. In some embodiments, the inner tubular member 231 and/or the outer tubular member 235 may increase in stiffness and exhibit increased shape-memory properties along their length distally toward the antenna assembly 12.

Shaft 110 may have a variable length from a proximal end of the antenna assembly 12 to a distal end of inflow/outflow junction 51, e.g., ranging from a length of about three feet to about six feet. Shaft 110 may have any suitable outer diameter “D”. In some embodiments, the shaft 110 may have an outer diameter “D” in a range from about 0.030 inches to about 0.110 inches. Various components of the shaft 110 may be formed of suitable, electrically-conductive materials, e.g., copper, gold, silver, or other conductive metals or metal alloys having similar conductivity values. Electrically-conductive materials used to form the cable assembly 15 may be plated with other materials, e.g., other conductive materials, such as gold or silver, to improve their properties, e.g., to improve conductivity, decrease energy loss, etc.

Cable assembly 15 may be any suitable, flexible transmission line. Cable assembly 15 may include an inner conductor 220, a dielectric material 222 coaxially surrounding the inner conductor 220, and an outer conductor 224 coaxially surrounding the dielectric material 222. Antenna assembly 12 may be formed from a portion of the inner conductor 220 that extends distal to the shaft 110 into the antenna assembly 12. Dielectric material 222 may be formed from any suitable, flexible, dielectric material, including, but not limited to, polyethylene, polyethylene terephthalate, polyimide, or polytetrafluoroethylene (PTFE) (e.g., Teflon®, manufactured by E. I. du Pont de Nemours and Company of Wilmington, Del., United States). Inner conductor 220 and the outer conductor 224 may be formed from any suitable electrically-conductive material. In some embodiments, the inner conductor 210 is formed from a first electrically-conductive material (e.g., stainless steel) and the outer conductor 224 is formed from a second electrically-conductive material (e.g., copper). In some embodiments, the outer conductor 224 is formed of one or more layers of braided metallic wires, e.g., to improve flexibility characteristics of the cable assembly 15. Cable assembly 15 may be provided with an outer coating or sleeve 226 disposed about the outer conductor 224. Sleeve 226 may be formed of any suitable insulative material, and may be may be applied by any suitable method, e.g., heat shrinking, over-molding, coating, spraying dipping, powder coating, baking and/or film deposition.

Electrosurgical power generating source 28 may be any generator suitable for use with electrosurgical devices, and may be configured to provide various frequencies of electromagnetic energy. In some embodiments, the electrosurgical power generating source 28 is configured to provide microwave energy at an operational frequency from about 300 MHz to about 2500 MHz. In other embodiments, the electrosurgical power generating source 28 is configured to provide microwave energy at an operational frequency from about 300 MHz to about 10 GHz.

Electrosurgical power generating source 28 may include a user interface 25 in operable communication with a processor unit (not shown). The processor unit may be any type of computing device, computational circuit, or any type of processor or processing circuit capable of executing a series of instructions that are stored in a memory. In an embodiment, a surgeon may input via the user interface 25 a selected power output, and the electrosurgical system 10 controls the probe 100 to automatically adjust the ablation volume by changing the operating frequency of the probe 100, e.g., based on the power level and/or level of reflected power.

Electrosurgical power generating source 28 may include an actuator 40. Actuator 40 may be any suitable actuator, e.g., a footswitch, a handswitch, an orally-activated switch (e.g., a bite-activated switch and/or a breath-actuated switch), and the like. Actuator 40 may be operably coupled to the processor by a cable connection (e.g., 17 shown in FIG. 1) or a wireless connection, e.g., a radiofrequency or infrared link. Electrosurgical power generating source 28 may include a database configured to store and retrieve energy applicator data, e.g., parameters associated with one or energy applicators. In use, the clinician may interact with the user interface 25 to preview operational characteristics of an energy-delivery device, such as, for example, probe 100.

User interface 25 may include a display device 21, e.g., a flat-panel graphic LCD (liquid crystal display), adapted to visually display one or more user-interface elements (e.g., 23 and 24 shown in FIG. 1). Display device 21 may include touchscreen capability, e.g., the ability to receive user input through direct physical interaction with the display device 21, e.g., by contacting the display panel of the display device 21 with a stylus or fingertip. A user-interface element (e.g., 23 and/or 24 shown in FIG. 1) may have a corresponding active region, such that, by touching the display panel within the active region associated with the user-interface element, an input associated with the user-interface element is received by the user interface 25. User interface 25 may include one or more controls 22, including without limitation a switch (e.g., pushbutton switch, toggle switch, slide switch) and/or a continuous actuator (e.g., rotary or linear potentiometer, rotary or linear encoder.) In an embodiment, a control 22 has a dedicated function, e.g., display contrast, power on/off, and the like. Control 22 may also have a function that may vary in accordance with an operational mode of the electrosurgical system 10. A user-interface element 23 may be positioned substantially adjacent to a control 22 to indicate the function thereof. Control 22 may also include an indicator, such as an illuminated indicator (e.g., a single- or variably-colored LED indicator).

Electrosurgical system 10 includes an inflow/outflow junction 51 coupled in fluid communication with the coolant supply system 150 via one or more coolant paths (e.g., 19 and 20 shown in FIG. 1), and coupled in fluid communication with the probe 100 via the flexible, fluid-cooled shaft 110. Coolant supply system 150 may be adapted to circulate coolant fluid “F” into and out of the inflow/outflow junction 51. Coolant source 18 may be any suitable housing containing a reservoir of coolant fluid “F”, and may maintain coolant fluid “F” at a predetermined temperature. For example, the coolant source 18 may include a cooling unit (not shown) capable of cooling the returning coolant fluid “F” from the antenna assembly 12 via the shaft 110.

Coolant fluid “F” may be any suitable fluid that can be used for cooling the cable assembly 15 and/or cooling or buffering the probe 100, e.g., deionized water, or other suitable cooling medium. Coolant fluid “F” may have dielectric properties and may provide dielectric impedance buffering for the antenna assembly 12. Coolant fluid “F” composition may vary depending upon desired cooling rates and the desired tissue impedance matching properties. Various fluids may be used, e.g., liquids including, but not limited to, water, saline, perfluorocarbon, such as the commercially available Fluorinert® perfluorocarbon liquid offered by Minnesota Mining and Manufacturing Company (3M), liquid chlorodifluoromethane, etc. In other variations, gases (such as nitrous oxide, nitrogen, carbon dioxide, etc.) may also be utilized as the cooling fluid. In yet another variation, a combination of liquids and/or gases, including, for example, those mentioned above, may be utilized as the coolant fluid “F”.

Coolant supply system 150 generally includes a first coolant path 19 leading from the coolant source 18 to the inflow/outflow junction 51, and a second coolant path 20 leading from the inflow/outflow junction 51 to the coolant source 18. In some embodiments, the first coolant path 19 includes a fluid-movement device 34 configured to move coolant fluid “F” through the first coolant path 19. The position of the fluid-movement device 34, e.g., in relation to the coolant source 18, may be varied from the configuration depicted in FIG. 1. Second coolant path 20 may additionally, or alternatively, include a fluid-movement device (not shown) configured to move coolant fluid “F” through the second coolant path 20. Examples of coolant supply system embodiments are disclosed in commonly assigned U.S. patent application Ser. No. 12/566,299 filed on Sep. 24, 2009, entitled “OPTICAL DETECTION OF INTERRUPTED FLUID FLOW TO ABLATION PROBE”.

FIG. 2A shows an embodiment of the inflow/outflow junction 51 of the electrosurgical system 10 shown in FIG. 1. Inflow/outflow junction 51 is adapted to be fluidly coupleable with the inner tubular member 231 and the outer tubular member 235 of the flexible, fluid-cooled shaft 110, and adapted to be connected in fluid communication with the coolant supply system 150. Inflow/outflow junction 51 may have a variety of suitable shapes, e.g., cylindrical, rectangular or the like.

Inflow/outflow junction 51 generally includes a housing 250A having an outer wall 285 and an inner wall 275 defining a plurality of interior chambers and/or openings or ports therein. In some embodiments, the outer wall 285 and the inner wall 275 cooperatively define a fluid inlet chamber 262 and a fluid outlet chamber 263, which are described later in this disclosure.

Housing 250A generally includes a fluid inlet port 52, a fluid outlet port 53, and a cable-entry port 59 all defined therein. Cable-entry port 59 includes an opening or passage 57 defined in the outer wall 285 configured to receive the cable assembly 15 therethrough. Cable-entry port 59 may include a channel or groove 58 adapted to receive an o-ring 211 configured to provide a fluid seal between the housing 250A and the cable assembly 15. In some embodiments, a cable-movement restrictor 215 may be affixed to or integrally formed with the housing 250A. Cable-movement restrictor 215 may be adapted to restrict movement of the cable assembly 15 and/or adapted to fixedly or releaseably secure the cable assembly 15 to the housing 250A. Cable-movement restrictor 215 may include any suitable fastening element, e.g., clips, clamps, or adhesive.

Fluid inlet port 52 may be adapted to be connected in fluid communication with the first coolant path 19. Fluid outlet port 53 may be adapted to be connected in fluid communication with the second coolant path 20. In some embodiments, the first coolant path 19 includes a coolant supply line 31 leading from the coolant source 18 to the fluid inlet port 52, and the second coolant path 20 includes a coolant return line 35 leading from the fluid outlet port 53 to the coolant source 18. Fluid inlet port 52 and the fluid outlet port 53 may be disposed at any suitable location along the outer wall of the housing 205. Fluid inlet port 52 and the fluid outlet port 53 may have any suitable configuration, including without limitation nipple-type inlet fittings, compression fittings, and recesses, and may include an o-ring type elastomeric seal.

In an embodiment, the fluid inlet port 52 is configured to define a first recess 252 in the outer wall 285 of the housing 250A, and the fluid outlet port 53 is configured to define a second recess 253 in the outer wall 285. First recess 252 and the second recess 253 may be of any suitable shape, e.g., rectangular, cylindrical, etc., and may include a groove adapted to receive an o-ring or other suitable sealing element. In some embodiments, the coolant supply line 31 is sealably connected with and extends into the first recess 252, and the coolant return line 35 is sealably connected with and extends into the second recess 253.

Housing 250A may be adapted to allow a portion of the presently disclosed flexible, fluid-cooled shaft 110 (e.g., a portion of the inner tubular member 231 and the cable assembly 15) to extend through the fluid outlet chamber 263 and/or the fluid inlet chamber 262. Fluid outlet chamber 263 is disposed in fluid communication with the fluid outlet port 53, and may be configured to be coupleable with the outer tubular member 235 of the shaft 110. Fluid outlet chamber 263 generally fluidly connects the fluid outlet port 53 to the fluid outflow conduit 335. In an embodiment, the outer wall 285 of the housing 250A is configured to define an opening 280 in the fluid outlet chamber 263 to allow the fluid outlet chamber 263 to be connectable in fluid communication with the fluid outflow conduit 335.

Fluid inlet chamber 262 is disposed in fluid communication with the fluid inlet port 52, and may be configured to be coupleable with the inner tubular member 231 of the shaft 110. Fluid inlet chamber 262 generally fluidly connects the fluid inlet port 52 to the fluid inflow conduit 331. In an embodiment, the inner wall 275 of the housing 250A is configured to define an opening 270 in the fluid inlet chamber 262 to allow the inlet chamber 262 to be connectable in fluid communication with the fluid inflow conduit 331. The shape and size of the fluid outlet chamber 263 and the fluid inlet chamber 262 may be varied from the configuration depicted in FIG. 2A.

Housing 250A may be configured to be sealingly engageable with the inner tubular member 231, e.g., to fluidly connect the fluid inlet chamber 262 and the fluid inflow conduit 331, and/or sealingly engageable with outer tubular member 235, e.g., to fluidly connect the fluid outlet chamber 263 and the fluid outflow conduit 335. Opening 270 defined in the inner wall 275 may be configured to receive the inner tubular member 231. Inner wall 275 may include an engagement portion 276 configured to engage an outer surface of the inner tubular member 231. Sealing engagement between the engagement portion 276 and the outer surface of the inner tubular member 231 may be provided, for example, by a sealing element, e.g., an o-ring, associated with the engagement portion 276. Sealing engagement may be provided by way of threads, external or internal, disposed on or within the inner tubular member 231 and threads disposed within or on the engagement portion 276. It is to be understood, however, that sealing engagement between the engagement portion 276 and the outer surface of the inner tubular member 231 may be provided by any suitable sealing means.

Opening 280 defined in the outer wall 285 may be configured to receive the outer tubular member 235. Outer wall 285 may include an engagement portion 286 configured to engage an outer surface of the outer tubular member 235. Sealing engagement between the engagement portion 286 and the outer surface of the outer tubular member 235 may be provided, for example, by a sealing element, e.g., an o-ring, associated with the engagement portion 286 of the outer wall 285. Sealing engagement may be provided by way of threads, external or internal, disposed on or within the outer tubular member 235 and threads disposed within or on the engagement portion 286. It is to be understood, however, that sealing engagement between the engagement portion 286 and the outer surface of the outer tubular member 235 may be provided by any suitable sealing means.

FIG. 2B shows an inflow/outflow junction 151 in accordance with the present disclosure. Inflow/outflow junction 151 includes a housing 250B that is similar to the housing 250A shown in FIG. 2A except for the configuration of the engagement portion 277 of the inner wall 275 and the configuration of the engagement portion 287 of the outer wall 285.

Engagement portion 277 is adapted to engage the outer surface of the inner tubular member 231 (e.g., similar to the engagement portion 276 shown in FIG. 2A). Engagement portion 277 includes a protrusion extending outwardly from the inner wall 275 adapted to engage an end portion of the inner tubular member 231. Inner tubular member 231 and the engagement portion 277 may be sealingly connected in any suitable fashion, e.g., by a heat-resistant adhesive material, or other suitable sealing material.

Engagement portion 287 is adapted to engage the outer surface of the outer tubular member 235 (e.g., similar to the engagement portion 286 shown in FIG. 2A). Engagement portion 287 includes a protrusion extending outwardly from the outer wall 285 adapted to engage an end portion of the outer tubular member 235. Outer tubular member 235 and the engagement portion 287 may be sealingly connected with a heat-resistant adhesive material, or other suitable sealing material.

FIG. 2C shows an inflow/outflow junction 251 in accordance with the present disclosure. Inflow/outflow junction 251 includes a housing 250C that is similar to the housing 250A shown in FIG. 2A except for the configuration of the engagement portion 278 of the inner wall 275 and the configuration of the engagement portion 288 of the outer wall 285.

Engagement portion 278 is adapted to engage the outer surface of the inner tubular member 231 (e.g., similar to the engagement portion 276 shown in FIG. 2A). Engagement portion 278 includes a generally L-shaped bracket 279 coupled to the inner wall 275 adapted to engage an end portion and the inner surface of the inner tubular member 231.

Engagement portion 288 is adapted to engage the outer surface of the outer tubular member 235 (e.g., similar to the engagement portion 286 shown in FIG. 2A). Engagement portion 288 includes a generally L-shaped bracket 289 coupled to the outer wall 285 adapted to engage an end portion and the inner surface of the outer tubular member 235.

FIG. 3 shows an embodiment of the probe 100 of the electrosurgical system 10 shown in FIG. 1. Probe 100 generally includes an antenna assembly 12 having a distal radiating portion “R” disposed within a chamber 338 (also referred to herein as a coolant chamber) defined by an end-cap assembly 360. Antenna assembly 12, which is described in more detail later in this disclosure, includes a proximal arm 370 and a distal arm 380.

End-cap assembly 360 includes a connector portion 368 and an end cap 364 disposed at the distal end of the connector portion 368 and coupled thereto. End cap 364 generally defines an interior chamber 365 therein. Connector portion 368 includes a substantially tubular, body member 361 defining an interior lumen disposed in fluid communication with the interior chamber 365 of the end cap 364. Connector portion 368 includes a distal portion 363, e.g., adapted for connection to the end cap 364, and a proximal portion 362, e.g., adapted for connection to the outer tubular member 235 of the shaft 110. The shape and size of the distal portion 363 and the proximal portion 362 of the connector portion 368 may be varied from the configuration depicted in FIG. 3.

Connector portion 368 may be formed of any suitable material. In some embodiments, the connector portion 368 may be formed of a composite material having low electrical conductivity, e.g., glass-reinforced polymers or ceramics. Outer tubular member 235 and the proximal portion 362 of the connector portion 368 may be sealingly connected with a heat-resistant adhesive material 302, or other suitable sealing material.

End cap 364 includes a tapered portion 320, which may terminate in a sharp tip 323 to allow for insertion into tissue with minimal resistance. Tapered portion 320 may include other shapes, such as, for example, a tip 323 that is rounded, flat, square, hexagonal, or cylindroconical. End cap 364 may be formed of a material having a high dielectric constant, and may be a trocar, e.g., a zirconia ceramic. In some embodiments, an interior chamber 365 defined by the end cap 364 includes a proximal chamber portion 366 and a distal chamber portion 367 fluidly coupled to the proximal chamber portion 366. The shape and size of the proximal chamber portion 366 and the distal chamber portion 367 may be varied from the configuration depicted in FIG. 3.

Probe 100 may be provided with a removable, protective cap 390 configured to cover at least a portion of the end-cap assembly 360. In some embodiments, the protective cap 390 is configured to cover the end cap 374. Protective cap 390 may be removeably disposed over the end cap 374 during deployment of the probe 100, e.g., to avoid injuring tissue. Protective cap 390 may be formed of any suitable material, e.g., plastic, by any suitable process.

Connector portion 368 may be adapted for releasable connection to the protective cap 390. In some embodiments, the distal end of the connector portion 368 and the proximal end of the protective cap 390 are releasably connectable by a screw-fitted connection. In an embodiment, the distal end of the connector portion 368 is provided with a series of external threads 369 configured to matingly engage with a series of internal treads 393 disposed at the proximal end of the protective cap 390. It will be appreciated that the proximal end of the protective cap 390 may be provided with external threads and the connector portion 368 may be provided with internal treads. It is to be understood that the protective cap 390 may be releasably connectable to the connector portion 368 in any suitable fashion.

Antenna assembly 12 includes a proximal arm 370 and a distal arm 380. Proximal arm 370 may have any suitable length “L2”, and the distal arm 380 may have any suitable length “L3”. In some embodiments, the proximal arm 370 may have a length “L2” in a range from about 0.05 inches to about 0.50 inches. In some embodiments, the distal arm 380 may have a length “L3” in a range from about 0.05 inches to about 0.50 inches.

Proximal arm 370 and the distal arm 380 may be formed of any suitable electrically-conductive material, e.g., metal such as stainless steel, aluminum, titanium, copper, or the like. In some embodiments, the proximal arm 370 is constructed from a piece of stainless steel, and may be coated in a high electrical conductivity, corrosion-resistant metal, e.g., silver, or the like. The proximal end 371 of the proximal arm 370 is electrically coupled to the distal end 325 of the outer conductor 224, e.g., by solder or other suitable electrical connection. In some embodiments, the proximal end 371 of the proximal arm 370 is coaxially disposed about the distal end 325 of the outer conductor 224. Proximal arm 370 generally defines a first chamber or cavity 372 therein longitudinally extending from the distal end 325 of the outer conductor 224. A dielectric material 310 may be disposed within the first cavity 372.

Distal arm 380 includes a proximal portion 381 and a distal portion 383. The distal portion 383 of the distal arm 380 is at least partially disposed within a cavity defined by the end cap 364. Distal arm 380 has a stepped configuration, such that the outer diameter of the distal portion 383 is less than the outer diameter of the proximal portion 381. In some embodiments, the proximal chamber portion 366 of the interior chamber 365 defined by the end cap 364 may be configured to receive the proximal portion 381 of the distal arm 380 therein, and the distal chamber portion 367 of the interior chamber 365 defined by the end cap 364 may be configured to receive the distal portion 383 of the distal arm 380 therein. Proximal chamber portion 366 and/or the distal chamber portion 367 may be adapted to allow coolant fluid (e.g., “F” shown in FIG. 1) to circulate around the proximal portion 381 and/or the distal portion 383.

In some embodiments, the distal arm 380 is constructed from a machined piece of stainless steel, and may be coated in a high electrical conductivity, corrosion-resistant metal, e.g., silver, or the like. The proximal portion 381 of the distal arm 380 defines a second chamber or cavity 382 therein. Dielectric material 310 may be disposed within the second cavity 382. The distal portion 383 of the distal arm 380 defines a third chamber or cavity 384 therein. Inner conductor 220 extends at least partially therethrough. Inner conductor 220 may be electrically coupled to the distal portion 383 by solder 307. In some embodiments, the distal portion 383 of the distal arm 380 includes one or more solder holes 389 defined therethrough.

Distal arm 380 and the proximal arm 370 align at a junction member 311 (which is generally made of a dielectric material 310) and are also supported by the inner conductor 220 that extends at least partially through the distal radiating portion “R”. Junction member 311 may be formed of low-loss plastic or any suitable elastomeric or ceramic dielectric material by any suitable process. In some embodiments, the junction member 311 is formed by over-molding and includes a thermoplastic elastomer, such as, for example, polyether block amide (e.g., Pebax®, manufactured by The Arkema Group of Colombes, France), polyetherimide (e.g., Ultem® and/or Extem®, manufactured by SABIC Innovative Plastics of Saudi Arabia) and/or polyimide-based polymer (e.g., Vespel®, manufactured by E. I. du Pont de Nemours and Company of Wilmington, Del., United States). Distal arm 380 and the proximal arm 370 may be insert molded with the junction member 311, such that the distal arm 380 and the proximal arm 370 are rigidly joined and spaced apart by the junction member 311, defining a feed gap “G” therebetween. In some embodiments, the feed gap “G” may be from about 1 mm to about 3 mm.

Probe 100 may include a balun structure “B” having a suitable length “L1”. Balun structure “B” is disposed proximal to and spaced apart a suitable length from the antenna assembly 12. In some embodiments, the balun structure “B” may be a quarter-wavelength, ¼λ, sleeve balun, or a ¾λ sleeve balun. Odd harmonics (e.g., ¼λ, ¾λ, etc.) may cause a current null at the balun entrance, which may maintain a desired radiation pattern.

Balun structure “B” includes a balun insulator 340 disposed about the outer conductor 224 of the cable assembly 15, and an electrically-conductive layer 350 (also referred to herein as a conductive balun sleeve) disposed about the balun insulator 340, or portions thereof. A portion 345 of the balun insulator 340 may extend distally beyond the distal end 355 of the electrically-conductive member 350, e.g., to enhance microwave performance of the probe 100 and/or provide a desired ablation pattern. Conductive balun sleeve 350 may be formed as a single structure and electrically coupled to the outer conductor 224, e.g., by solder or other suitable electrical connection. In some embodiments, the proximal end 352 of the conductive balun sleeve 350 may be adapted to allow for connection, e.g., electrically and mechanically, to the outer conductor 224.

Balun structure “B”, according to the embodiment shown in FIG. 3, includes a balun short 351 disposed at the proximal end of the balun insulator 340. Balun short 351 may be formed of any suitable electrically-conductive materials, e.g., copper, gold, silver or other conductive metals or metal alloys. In some embodiments, the balun short 351 has a generally ring-like or truncated tubular shape. Balun short 351 is electrically coupled to the outer conductor 224 of the feedline or cable assembly 15 by any suitable manner of electrical connection, e.g., soldering, welding, or laser welding. Balun short 351 is electrically coupled to the balun outer conductor 350 by any suitable manner of electrical connection.

Balun insulator 340 may be formed of any suitable insulative material, including, but not limited to, ceramics, water, mica, polyethylene, polyethylene terephthalate, polyimide, polytetrafluoroethylene (PTFE) (e.g., Teflon®, manufactured by E. I. du Pont de Nemours and Company of Wilmington, Del., United States), glass, metal oxides or other suitable insulator, and may be formed in any suitable manner. Balun insulator 340 may be grown, deposited or formed by any other suitable technique. In some embodiments, the balun insulator 340 is formed from a material with a dielectric constant in the range of about 1.7 to about 10.

Electrically-conductive layer 350 may be formed of any suitable electrically-conductive material, e.g., metal such as stainless steel, titanium, copper, etc., and may be formed in any suitable manner. In some embodiments, the electrically-conductive layer 350 has a length of about 0.1 inches to about 3.0 inches. The shape and size of the conductive balun sleeve 350 and balun insulator 340 may be varied from the configuration depicted in FIG. 3.

Probe 100 generally includes a coolant chamber 338 defined about the antenna assembly 12. Coolant chamber 338 is adapted to circulate coolant fluid (e.g., “F” shown in FIG. 1) around the antenna assembly 12 (as generally indicated by the arrows in FIG. 3) and disposed in fluid communication with the fluid inflow conduit 331 and the fluid outflow conduit 335. In some embodiments, the coolant chamber 338 is defined by the end-cap assembly 360 and includes an interior lumen defined by the substantially tubular, body member 361 of the connector portion 368. Coolant chamber 338 may additionally, or alternatively, include an interior chamber 365 defined by the end cap 364. The shape and size of the coolant chamber 338 may be varied from the configuration depicted in FIG. 3.

During microwave ablation, e.g., using the electrosurgical system 10, the probe 100 is inserted into or placed adjacent to tissue and microwave energy is supplied thereto. Ultrasound or computed tomography (CT) guidance may be used to accurately guide the probe 100 into the area of tissue to be treated. Probe 100 may be placed percutaneously or surgically, e.g., using conventional surgical techniques by surgical staff. A clinician may pre-determine the length of time that microwave energy is to be applied. Application duration may depend on many factors such as tumor size and location and whether the tumor was a secondary or primary cancer. The duration of microwave energy application using the probe 100 may depend on the progress of the heat distribution within the tissue area that is to be destroyed and/or the surrounding tissue. Treatment of certain tumors may involve probe repositioning during the ablation procedure, such as where the tumor is larger than the probe or has a shape that does not correspond with available probe geometry or radiation pattern.

In operation, microwave energy having a wavelength, lambda (λ), is transmitted through the antenna assembly 12, e.g., along the proximal arm 370 and the distal arm 380, and radiated into the surrounding medium, e.g., tissue. The length of the antenna for efficient radiation may be dependent on the effective wavelength, λ_(eff), which is dependent upon the dielectric properties of the treated medium. Antenna assembly 12 through which microwave energy is transmitted at a wavelength, λ, may have differing effective wavelengths, λ_(eff), depending upon the surrounding medium, e.g., liver tissue, as opposed to breast tissue.

FIG. 4 shows an inflow/outflow junction 451 adapted to be connected in fluid communication with a portion of a flexible, extendable/retractable fluid-cooled shaft 410 according to an embodiment of the present disclosure. Inflow/outflow junction 451 includes a housing 450 configured to be releaseably and sealably coupleable with the cable assembly 15 shown in FIG. 1. Housing 450 includes a fluid inlet port 452, a fluid outlet port 453, a fluid inlet chamber 462, a fluid outlet chamber 463, a tubular sleeve member 489, and a releasable, cable-movement restrictor 415.

Releasable, cable-movement restrictor 415 includes a sealing element 411, e.g., an o-ring, and a rotatable member 416. In some embodiments, rotation of the rotatable member 416 in a first direction (e.g., a clockwise direction) effects a compression force on the sealing element 415 to restrict movement of the cable assembly 15 and to provide a fluid seal. In some embodiments, rotation of the rotatable member 416 in a second direction (e.g., a counter-clockwise direction) releases the compression force on the sealing element 411 to allow movement of the cable assembly 15, thereby allowing extension and/or retraction of the outer tubular member 445 and the inner tubular member 441 of the shaft 410.

Tubular sleeve member 489 of the presently disclosed housing 450 is generally configured to house a portion of the expandable/retractable shaft 410, and may have any suitable length “L4”. Fluid inlet port 452, fluid outlet port 453, fluid inlet chamber 462, and fluid outlet chamber 463 shown in FIG. 4 are similar to the fluid inlet port 52, fluid outlet port 53, fluid inlet chamber 262, and fluid outlet chamber 263 shown in FIG. 1, respectively, and further description thereof is omitted in the interests of brevity.

Flexible, extendable/retractable fluid-cooled shaft 410 is adapted to allow for selective adjustment of the length of the fluid-cooled shaft 410. In some embodiments, the shaft 410 may be selectively adjustable to any length between a first length (e.g., “L5” shown in FIG. 5), when the shaft 410 is in its most retracted use configuration, and a second length (e.g., “L6” shown in FIG. 5) when the shaft 410 is in its most extended use configuration. Flexible, extendable/retractable fluid-cooled shaft 410 generally includes an inlet sleeve 431, an outlet sleeve 435, an inner tubular member 441 coaxially disposed about and slideably coupled to the inlet sleeve 431, and an outer tubular member 445 coaxially disposed about and slideably coupled to the outlet sleeve 435. In some embodiments, a first lubricous sleeve 408 may be disposed between the inner tubular member 441 and the inlet sleeve 431, and a second lubricous sleeve 409 may be disposed between the outer tubular member 445 and the outlet sleeve 435.

First lubricous sleeve 408 and the second lubricous sleeve 409 may be formed of any suitable non-conductive insulator, e.g., a TEFLON® sleeve. First lubricous sleeve 408 and/or the second lubricous sleeve 409 may be selected based on materials properties, e.g., density and lubricity, to allow for sliding of the inner tubular member 441 over the inlet sleeve 431 and/or sliding of the outer tubular member 445 over outlet sleeve 435. First lubricous sleeve 408 and/or the second lubricous sleeve 409 may additionally, or alternatively, be selected to prevent damage and/or minimize wear to the inner tubular member 441 and/or the outer tubular member 445. First lubricous sleeve 408 and/or the second lubricous sleeve 409 may be formed of a lubricous polymeric material, such as a high-density polyolefin (e.g., polyethylene), polytetrafluoroethylene (a.k.a. PTFE or TEFLON®, manufactured by E. I. du Pont de Nemours and Company of Wilmington, Del., United States), or polyurethane. First lubricous sleeve 408 and/or the second lubricous sleeve 409 may be formed by heat-shrinkage, extrusion, molding, dip coating, or other suitable process. In some embodiments, the insulator sleeve 270 may include a surface coating formed of highly hydrophilic, low-friction polymer, such as polyvinylpyrrolidone, polyethyleneoxide, polyhydroxyethylmethacrylate, or copolymers thereof.

In some embodiments, the shaft 410 may be configured in its most retracted use configuration when the proximal end of the inner tubular member 441 is disposed proximally in substantial alignment with the proximal end of the inlet sleeve 431 and/or the proximal end of the outer tubular member 445 is disposed proximally in substantial alignment with the proximal end of the outlet sleeve 435.

FIG. 5 shows the flexible, extendable/retractable fluid-cooled shaft 410 and the inflow/outflow junction 451 of FIG. 4 in its most retracted use configuration in accordance with an embodiment of the present disclosure. In its most retracted use configuration, the fluid-cooled shaft 410 may have any suitable length “L5”. In some embodiments, the flexible, extendable/retractable fluid-cooled shaft 410 may be provided with one or more shape-retention elements 510 adapted to provide resistance to change in the outer diameter of the shaft 410, e.g., during expansion/retraction of the shaft 110 and/or during the circulation of coolant fluid therethrough. Shape-retention elements 510 may be disposed around the outer tubular member 445 and/or slideably coupled to the outer tubular member 445.

FIG. 6 shows the flexible, extendable/retractable fluid-cooled shaft 410 and the inflow/outflow junction 451 of FIG. 4 in its most extended use configuration in accordance with an embodiment of the present disclosure. In its most retracted use configuration, the fluid-cooled shaft 410 may have any suitable length “L6”.

The presently disclosed energy-delivery devices with a flexible, fluid-cooled shaft are capable of directing energy into tissue, and may be suitable for use in a variety of procedures and operations. The above-described energy-delivery device embodiments may be suitable for utilization with hand-assisted, endoscopic and laparoscopic surgical procedures. The above-described energy-delivery device embodiments may be suitable for utilization in open surgical applications.

Various embodiments of the presently disclosed energy-delivery device with a flexible, fluid-cooled shaft may allow the surgeon to deploy an ablation probe, e.g., between closely spaced boundaries of tissue structures, to reach the location of the ablation site. The above-described energy-delivery device embodiments may allow the surgeon to manually deploy an ablation probe having a flexible, fluid-cooled shaft with his/her hand to place the probe at difficult-to-reach locations, such as, for example, the dome of the liver near the top of the diaphragm. Various embodiments of the presently disclosed energy-delivery devices with a flexible, fluid-cooled shaft including a length of cable assembly surrounded by inner and outer tubular members adapted to circulate coolant fluid therethrough may lessen the potentially unwanted heat transfer from the cable assembly to the patient's body during a procedure, e.g., an ablation procedure.

The above-described inflow/outflow junction embodiments are adapted to be coupled in fluid communication with the inner and outer tubular members of the above-described flexible, fluid-cooled shaft embodiments, and adapted to be coupled in fluid communication with a suitable coolant supply system. The presently disclosed inflow/outflow junctions embodiments may be adapted to be coupled in fluid communication with a coolant supply system and adapted to selectively allow movement of a cable assembly therethrough, e.g., to facilitate the extension/retraction of an extendable/retractable fluid-cooled shaft.

Electrosurgical systems including an energy-delivery device with a flexible, fluid-cooled shaft according to embodiments of the present disclosure may be fluidly coupled to a coolant supply system via the above-described inflow/outflow junction embodiments.

Although embodiments have been described in detail with reference to the accompanying drawings for the purpose of illustration and description, it is to be understood that the inventive processes and apparatus are not to be construed as limited thereby. It will be apparent to those of ordinary skill in the art that various modifications to the foregoing embodiments may be made without departing from the scope of the disclosure. 

1-14. (canceled)
 15. A tissue treatment device, comprising: a housing; and a shaft coupled to the housing, the shaft including: an outer tubular member defining a fluid outflow conduit; an inner tubular member defining a fluid inflow conduit; an inlet sleeve slidingly coupled to the inner tubular member; and an outlet sleeve coupled to the outer tubular member.
 16. The tissue treatment device according to claim 15, wherein the outlet sleeve is configured to adjust a length of the shaft.
 17. The tissue treatment device according to claim 15, wherein the housing includes an inlet chamber fluidly coupled to the fluid inflow conduit.
 18. The tissue treatment device according to claim 15, wherein the housing includes an outlet chamber fluidly coupled to the fluid outflow conduit.
 19. The tissue treatment device according to claim 15, further comprising a cable assembly extending through the shaft, the cable assembly including an inner conductor, an outer conductor, and a dielectric material disposed between the inner conductor and the outer conductor.
 20. The tissue treatment device according to claim 15, wherein the outer tubular member is disposed within a tubular sleeve member coupled to the housing.
 21. The tissue treatment device according to claim 15, wherein the outlet sleeve is slidingly coupled to the outer tubular member.
 22. The tissue treatment device according to claim 15, further comprising a lubricious sleeve disposed between the inner tubular member and the inlet sleeve.
 23. The tissue treatment device according to claim 15, further comprising a shape-retention element disposed around the outer tubular member.
 24. The tissue treatment device according to claim 15, further comprising a balun structure disposed within the shaft, the balun structure including a balun insulator and a conductive balun sleeve disposed on the balun insulator.
 25. A fluid-cooled shaft for a tissue treatment device, comprising: an outer tubular member defining a fluid outflow conduit; an inner tubular member defining a fluid inflow conduit; an inlet sleeve slidingly coupled to the inner tubular member; and an outlet sleeve slidingly coupled to the outer tubular member.
 26. The fluid-cooled shaft according to claim 25, wherein the outlet sleeve is configured to adjust a length of the fluid-cooled shaft.
 27. The fluid-cooled shaft according to claim 25, further comprising a cable assembly extending through inner tubular member, the cable assembly including an inner conductor, an outer conductor, and a dielectric material disposed between the inner conductor and the outer conductor.
 28. The fluid-cooled shaft according to claim 25, further comprising a lubricious sleeve disposed between the inner tubular member and the inlet sleeve, the lubricious sleeve configured to facilitate sliding of the inlet sleeve relative to the inner tubular member.
 29. The fluid-cooled shaft according to claim 25, further comprising a lubricious sleeve disposed between the outer tubular member and the outlet sleeve, the lubricious sleeve configured to facilitate sliding of the outlet sleeve relative to the outer tubular member.
 30. The fluid-cooled shaft according to claim 25, further comprising a shape-retention element disposed around the outer tubular member.
 31. The fluid-cooled shaft according to claim 25, further comprising a balun structure disposed within the inner tubular member, the balun structure including a balun insulator and a conductive balun sleeve disposed on the balun insulator.
 32. A fluid-cooled shaft for a tissue treatment device, comprising: an outer tubular member defining a fluid outflow conduit; an outlet sleeve configured to slide relative to the outer tubular member; an inner tubular member defining a fluid inflow conduit; and an inlet sleeve configured to slide relative to the inner tubular member.
 33. The fluid-cooled shaft according to claim 32, further comprising a lubricious sleeve disposed between the inner tubular member and the inlet sleeve.
 34. The fluid-cooled shaft according to claim 32, further comprising a lubricious sleeve disposed between the outer tubular member and the outlet sleeve. 